Electronic medication compliance monitoring system and associated methods

ABSTRACT

A system and method for monitoring a patient&#39;s compliance with a medication regimen includes an electronic tag integral with or attached to a medicine delivery device such as a capsule, the tag having an antenna and a receiver/transmitter, the system also including a reader positioned externally for detecting the presence and location of the delivery device in the patient.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation of U.S. application Ser. No.14/726,899 filed Jun. 1, 2015, now U.S. Pat. No. 9,743,880 issued onAug. 29, 2017, which is a continuation of U.S. application Ser. No.12/881,572 filed Sep. 14, 2010, now U.S. Pat. No. 9,047,746 issued onJun. 2, 2015, which is a continuation-in-part of application Ser. No.11/458,815 filed Jul. 20, 2006, now U.S. Pat. No. 7,796,043 issued onSep. 14, 2010, which claims priority to U.S. Provisional ApplicationSer. Nos. 60/700,963, 60/734,483 and 60/746,935, filed Jul. 20, 2005,Nov. 8, 2005 and May 10, 2006, respectively, the entire contents ofwhich applications are herein incorporated by reference in theirentirety.

FIELD OF THE INVENTION

The present invention relates to electronic systems and methods formonitoring medication compliance.

BACKGROUND OF THE INVENTION

Non-compliance of patients to drug regimens prescribed by physicians cancause a multiplicity of problems, including negative patient outcomes,higher healthcare costs and an increased risk of the spread ofcommunicable diseases. Compliance monitoring is also critical in, forexample, pharmaceutical clinical trials, geriatrics and mentalhealth/addiction medicine. Poor medication compliance has a significantnegative impact on patients, pharmaceutical manufacturers and thehealthcare system in general. Non-compliant patients suffer fromincreased mortality, increased recurrence of chronic conditions andincreased hospital and nursing home admissions. By some estimates, asmuch as 25% of all healthcare costs could be avoided if patientsreliably took their prescribed medications.

Annual drug development spending has increased more than twelve times ininflation-adjusted dollars over the past three decades. Clinical trialsconsume a major portion of the development time and costs of introducinga new drug into the market. Knowing with certainty a patient's adherencesignificantly improves the understanding of the results from a clinicaltrial in terms of safety, efficacy, dose response relationship,pharmacodynamics, side effects and other results. For instance, in abeta-blocker heart attack trial the death rate was reported at 13.6% insubjects whose compliance was less than 75% compared to 5.6% in subjectswhose compliance was over 75%. None of the existing methods of measuringadherence offer both a qualitative and a quantitative measure withproof-positive detection of ingestion of the medication. Accordingly,measuring medication regimen compliance continues to be a major problem.The only statistical recourse is to enroll large numbers of patients,which dramatically increases the cost of clinical drug trials that inturn increases the cost of the final marketed medication.

Compliance monitoring also provides significant benefits in market areaswhere patient adherence to a drug therapy protocol is vital topreventing or avoiding high-cost consequences for the patient orcommunity. Strict regimen adherence is important for preventingemergence of drug-resistant strains of infectious diseases that canoccur when proper dosing schedules are not followed. Such resistantstrains result in increased transmission, morbidity and mortality andare more expensive to treat or cure, often by one or two orders ofmagnitude.

A traditional method of increasing compliance is direct observance, butthis is obviously difficult to administer and impractical on a largescale. Other techniques include blood sampling, urine sampling,biological marker detection, self-reporting, pill counting, electronicmonitoring and prescription record review. These techniques are eitherinvasive or prone to tampering.

In vivo biotelemetry and monitoring have been used for monitoringembedded oxygen, sensing glucose levels, fetal monitoring and hormonemeasuring. Passive radio-frequency identification (RFID) techniques havebeen suggested to provide biotelemetry by including external sensorsinto existing commercial systems. However, RFID was not designed tooperate in vivo, and the transmission of electromagnetic signals fromembedded or internal sensors is hampered by attenuation and reflectionsfrom the body.

Therefore, it would be beneficial to provide an active electronicdevice, system and method for non-invasively monitoring drug compliancein a facile manner.

SUMMARY OF THE INVENTION

The present invention is directed to an electronic drug compliancemonitoring system and associated methods that utilizes a pill having anactive electronic transmission capability and external means forreceiving that transmission to sense the presence of the pill in thepatient's internal organs.

It is believed that the present invention has several advantages overcurrently known methodologies. For example, the monitor documents thatthe prescribed medication was actually present in the digestive system,whereas not even directly observed therapy can conclusively determinethat the patient swallowed the pill. The system can be used withmedication dispensers, timers, reminders, external communications, anddatabase systems to create a complete medication compliance monitoringsystem. The system provides factual evidence of patient's compliance tothe regimen, medication, knowledge that is critical, for example, toassessing the outcome of a clinical trial including the systematicremoval of non-compliant subject data. Trials that pay subjects toparticipate in clinical studies can corroborate compliance. Further, thesystem permits remote patient monitoring whereby the monitor can beintegrated into a wireless system communicating directly with a centraldatabase, reducing costs by minimizing required patientmonitoring/interaction. Finally, the system is noninvasive and does notrequire the collection of a bodily fluid.

The features that characterize the invention, both as to organizationand method of operation, together with further objects and advantages,will be better understood from the following description used inconjunction with the accompanying drawing. It is to be expresslyunderstood that the description and drawing are for the purpose ofillustration and is not intended as a definition of the limits of theinvention.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a schematic diagram of the medication compliance system of thepresent invention.

FIG. 2A is one embodiment of a capsule having a planar substrate with anantenna and electronics wrapped about a portion of the capsule.

FIG. 2B illustrates a capsule having a multiple-coil antenna wrappedabout its periphery.

FIG. 2C illustrates a capsule having a single-coil antenna wrapped abouta portion of its periphery.

FIG. 3 is a schematic chart that illustrates the use of an electroniccapsule with a wristband reader that is in communication with a cellphone, and which in turn can be used to forward information to a datacollection center.

FIG. 4 is a schematic diagram illustrating the onboard electronicsfitted with an electronic pill or capsule like that shown in FIGS. 1,2A-2D and 3.

FIGS. 5A and 5B illustrate techniques used to mate an electronic tagshown in FIGS. 1 and 3 with the inside surface of a capsule (FIG. 5A) orthe outer surface (FIG. 5B).

FIGS. 6A, 6B and 6C are schematic side views illustrating the layersused to fabricate an electronic tag in accordance with differentembodiments of this invention.

FIG. 7 is a circuit diagram for an exemplary activation switch circuitusing a conductive sensor with a NMOSFET transistor.

FIG. 8 is a circuit diagram for an exemplary deactivation switch circuitusing a MOSFET transistor.

FIG. 9 is a circuit diagram for an exemplary MOSFET sensor-basedbio-switch.

FIG. 10A is a top perspective view of an ingestible switch in accordancewith the present invention utilizing a hydrogel circuit breaker.

FIG. 10B depicts the switch of FIG. 10A, with a swollen hydrogel circuitbreaker after exposure to gastrointestinal fluids.

FIG. 11 is a schematic side view of a galvanic gastric sensor forutilization with the electronic tag shown in FIGS. 1 and 3.

FIG. 12A is a summary of the results of testing of several phosphateelectrodes at different modes.

FIGS. 12B and 12C are coded charts depicting the results set forth inFIG. 12A for a 20K Ohm load and a 1K Ohm, respectively.

FIG. 13 is a block diagram illustrating the electronics associated withthe tag integrated circuit.

FIG. 14 is a block diagram illustrating the overall inlink and outlinkcommunications between the electronic tag taken internally by a patient,and the external reader utilized to communicate with the tag.

FIG. 15 is a timing chart illustrating the periodic transmissions fromthe reader to the tag and the data bursts from the tag to the reader.

FIG. 16 is a chart depicting the content of the inlink transmission fromthe reader to the tag.

FIG. 17 is a chart depicting the content of information contained in thedata bursts from the tag to the reader.

FIG. 18 depicts a timing chart for uplink transmissions from multipletags to the reader.

FIG. 19 is a further block diagram of the overall system, illustrating aspecific example of conductive transmissions from the reader to the tagat 4 MHz and radiative outlink transmissions from the tag to the readerat 400 MHz by way of example.

FIG. 20 is another timing diagram illustrating the operation of thesystem of the present invention.

FIGS. 21A and 21B are block diagrams illustrating further aspects of theoperation of the system.

FIG. 22 is a side view illustrating an alternate construction for theelectronic capsule to permit a portion of the electronics to be carriedwithin the capsule.

FIG. 23 is an exploded illustration depicting, from left to right, theattachment of an integrated circuit chip to the tag connected to the lowfrequency and high frequency antenna areas, and the wrapping of the tagabout a capsule (right hand side).

FIGS. 24A and 24B depict exemplary constructions of a capsule with a tagin accordance with this invention.

FIG. 25 is a top view of the tag, illustrating various dimensions andsmall component details and a wrapped configuration.

FIG. 26 is a cross-sectional side view of the tag, illustrating variousdimensions associated with the elements depicted in schematic form inFIGS. 6A and 6B.

FIG. 27 sets forth representative dimensions of the capsule and tag.

FIG. 28 is a top view of a wrist band reader feature shown in FIG. 3.

FIG. 29 depicts a patch reader wearable by a patient.

FIG. 30 depicts a pill container having an on-board reader.

FIG. 31 is a block diagram of the reader 19 in FIG. 1.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

A description of the preferred embodiments of the present invention willnow be presented with reference to FIGS. 1-30.

Noting FIG. 1, a system 10 for monitoring medication compliance in apatient 16 comprises an electronic sensor, preferably in the form of asmall monitor or reader 11 that includes an RF transceiver 12 and one ormore antennas 13. The antenna 13 can be external or internal to themonitor 11 and can be implemented in a variety of ways as known in theart, including an on-chip antenna or simple pads or electrical contactsthat function as an antenna. The reader 11 detects the presence of anelectronic pill 14 in, for example, the gastrointestinal tract of thepatient 16. As shown the electronic pill 14 has a tag 15 attached to orpart of the pill 14. For purposes of this disclosure, the term “pill”can include a capsule or other form of medication administration ortesting. The system 10 is designed to detect the pill 14 when located inthe patient's mouth M, esophagus E, stomach S, duodenum D, intestines Ior rectum R.

With continued reference to FIG. 1, the system 10 includes a tag 15fixed with the pill 14, either internally or along the outer surface, orboth. After ingestion of the pill 14, the tag 15 is made electronicallyactive and begins communication with the external reader 11. Theexternal reader 11 in one embodiment is in a housing 19 worn by orattached with the patient 16 so as to be comfortable and easy to wearcontinuously to ensure it is always with the patient.

The electronic pill 14 comprises an orally ingestible and biocompatibledrug-transporting device with embedded or attached electronic circuitsthat communicates with the external wireless reader 11. As described ingreater detail below, the electronic pill 14 uses, for example, asilicon-based integrated circuit and/or other passive components such ascoil antennae and capacitors. The circuit can incorporate millions oftransistors, patterned through various semiconductor processing steps,to provide an enormous amount of intelligence. For instance, theelectronic pill 14 can store a patient's medical history in addition todetailed information about a drug being administered, provide a uniqueidentification number, and implement advanced communication circuits andprotocols to reliably transmit data to an external wireless reader 11.

Turning now to FIG. 2A, the electronic pill 14 preferably comprises adrug-transporting device, such as a capsule 17 that has associatedtherewith the electronic tag 15. Noting FIG. 1, a signal 18 received bythe reader 11 from the electronic circuit 30 after ingestion of thecapsule 17 is thus indicative of medication compliance. The term“drug-transporting device” is not intended as a limitation, and othercompositions and devices for delivering medication are intended to besubsumed hereinto as known in the art. Alternatively, the capsule 17 maybe devoid of medication to serve as a placebo during a drug trial.

Referring again to FIG. 2, the electronic components of the electronicpill 14 are capable of wireless transmission and reception over shortdistances (i.e., in the range of 20-30 cm). The electronic components inthe circuit 20 (i.e., antenna 21, power source 22, and silicon chip 23),once hermetically sealed and packaged, is small enough to fit inside oron the outside wall of the capsule 17. This level of miniaturization isfeasible owing to integration and circuit scaling trends associated withstandard CMOS technologies.

With continued reference to FIG. 2A, a small chip or other electronics47 is attached to the substrate 45 as well. This chip 47 provides agreat deal of functionality including but not limited to two waycommunication and complex protocols, energy harvesting (mechanical,electrical, etc), sensing of conditions such as location of the tag viapH, chlorine content, etc., encryption, and identification code storageand transmission.

Referring now to FIG. 3, the complete system is principally composed ofa Data Reader 111 and multiple tags 15 attached to medication 14.Bidirectional data 50/52 is exchanged between the reader 111 and the tag15. The reader 111 probes the one or more tags 15 inside the body 10 andcoordinates the communication to allow multiple ingested tags tocommunicate simultaneously, sequentially, or in other ways to permitmultiple communication pathways. The tags 15 communicate their uniqueidentification data and whether they are in the GI tract. The reader 111then provides output data 58 to a user interface 54 such as a laptop orsmartphone enabling real-time upload 59 of medication events to a remotedatabase 60 or other location.

The data link from the reader to tag 50 is defined as the “in-link”path. Preferentially, in-link data to the tag includes synchronization,signaling, address, and tag configuration information. Preferentially,the reader 111 transmits information by way of differential metallicskin contacts. The signal passes through the body and is sensed by thetag through a differential probe network.

The data link from the tag to the reader 52 is defined as the “out-link”path. Preferentially, the out-link data to the reader includesgastrointestinal (GI) sensing, pharmaceutical, adherence, signal level,and address information. Preferentially, the out-link channel 52 iscomposed of a radio frequency signal traveling through both the body 10and the free space between the body and reader antenna. A small antenna(REF) on the tag 15 radiates the out-link signal 52 which is received atthe reader 111. The reader 111 is capable of receiving signals 52 frommultiple tags 14 simultaneously.

All of these components work together to complete a system that canaccurately detect a medication event, including the time of ingestion,the dosage, and specific identification of the medication. Thisinformation is then used to verify critical compliance with drugtherapy. This data can also be used in combination with other patientdata to improve adherence and treatment outcomes.

In the embodiment shown in FIG. 2B, the capsule 17 has an antenna 40printed or attached that can be detected externally. In one suchembodiment, an externally induced magnetic field with a time-varyingoscillatory component impinging upon a resonant tank in the pill (i.e.,formed by a transponder coil antenna and a parallel capacitor located inthe tag 15) causes the current circulating in the tank to increase. Thepeak current at the frequency of resonance can induce a small butdetectable change in the reader coil impedance. Since the coils are onlyloosely coupled, the resonant peak detection experiment can characterizethe range over which this effect can be used to detect the presence of apill.

Marker/Tag Detail and Manufacturing

The following sections describe the detailed construction of the tag 15.Referring to FIG. 4, the tag 15 comprises a body interface and antenna203 that allows for the in-link 50 and out-link 202 communication. Theingestion detection subsystem 208 utilizes the body interface andantenna system 203 to determine when the medication actually resides inthe body 10 and in particular in the digestive tract M, E, S, D, I, R. Areceive subsystem 204 implements the in-link 50 communication andinterfaces between the body interface and antenna subsystem 203 and acontrol subsystem 209. A transmission subsystem 206 implements theout-link 52 communication and interface between the control subsystem209 and the body interface and antenna subsystem 203. An energyharvesting subsystem 205 captures energy from either the body interface203 or from the environment that the tag 15 resides in, for example themotion or temperature of the device. The energy harvesting subsystem 205provides energy which is stored in an energy storage system 207 and tothe tag 15 in general to operate the components and provide sufficientpower for outlink 52 transmission. The control subsystem 209 coordinatesand controls the differing components of the tag 15 and implements anycommunication protocol, sensor measurements, maintains tag memory forvarious identification information, and implements any otherfunctionality required by the tag 15. The tag 15 can be attached to themedicine in a variety of ways, either by being built into themedication, build onto the medication, being printed onto themedication, or by being attached onto the outside or inside of themedication carrier (i.e. a capsule). A preferred embodiment is to buildthe tag 15 on a biocompatible substrate 45 that can be built in highquantities and then later attached or built into a capsule 17, forexample.

Substrate (Printing and Tag)

Referring now to FIGS. 5A and 5B, in another embodiment of the tag 43and the antenna 44 are printed on a flexible substrate 45 that isbiodegradable and digestible, such as a flat sheet-like material, andincludes an electronic chip 47 mounted on the substrate. This substrate45 is then placed on or wrapped around the capsule 46. The antenna 44 ispreferably printed in a way that when the material 45 is wrapped arounda capsule 46, connections can be made from one end of the sheet 45 tothe other, thus forming the antenna 44 as a continuous loop. Printing onboth sides of the material 45 simplifies this process by using atechnique similar to circuit board manufacturing with through-holes.Preferably, the substrate should have sufficient rigidity formanufacturing and attachment, be easily and safely digested, be flexiblefor wrapping around a pill or capsule, and withstand temperaturesrequired for manufacturing and sterilization.

There are relatively few materials for substrates 45 and 74 that areboth easily and safely digested and can also withstand temperaturesrequired for bonding the chips 47 and 71 to the antennae 44 and 72 (upto 190° C.) or the sintering of metallic inks. In one embodiment, anenteric coating commonly used in colonic-targeted drug release, isutilized to create a flat and flexible substrate that meets theserequirements and has been used in prototype tags.

Enteric coatings are commercial materials with good flexibility andproven biocompatibility. They are currently used in aspirin,acetomenophin and other drugs that upset the stomach, as they resistdisintegration at low pH. Enteric coatings usually begin to disintegrateat a pH above 5.5 or higher, which is the typical pH of the duodenum andsmall intestine. Enteric coatings include but are not limited topolymethacrylate-polymethylmethacrylate (PMA-PMMA) copolymers andcellulose acetate phthalate (CAP), which are commercial coatings undernames of “Eudragit” and “Aquacoat CPD” that are readily available aspre-mixed solutions.

Referring now to FIG. 6A, in another embodiment, the substrate 45 can bemanufactured with a coated paper to create a biocompatible coated papersubstrate system 260 to provide more advantageous properties. A papersubstrate 82 coated with a coating 254 provides improved mechanicalproperties, increase printing strength, reduced dissolution time, andallows for alternative printing methods, while maintainingbiocompatibility. Enteric coated paper provides a smooth texture 256 forthe paper 82 and allows for antenna patterns 266 to be easilytransferred onto it. The paper 82 also breaks up rapidly once thecoating 254 dissolves. Preferentially, the paper 82 is coated on allsides, but in some implementations coating only the top of the paper isrequired. In addition, a biocompatible adhesive 252 is applied to thebottom of the paper when the tag 15 will be applied to the outside ofthe medication. When adhesive 252 is included, a protective backing 258is used to simplify handling and attachment to the medication.

The biocompatible coated paper system 260 of FIG. 6A addressesmanufacturing problems of electroplating/electroetching on biodegradablesubstrates. Preferentially, biocompatible paper 82 is a mixture ofbiodegradable materials distributed in impregnated and/or on coated thepaper in a number of ways. Paper 82 can be any substance that can beused as a flexible and strong biocompatible substrate in the dry statebut weakens in the wet state. Rice papers, pulp papers, plant-basedfiber papers including linen papers are all substrates that can be usedwith a biocompatible material coating or impregnation. The paper 82itself is also biocompatible. The biocompatible substances 254 used forcoating or impregnating the paper alter the dissolution properties,thermal properties, mechanical properties, biodegradation rates andother properties of the paper 82. The biodegradable materials includedin the construction of the biodegradable substrate 260 allow fordigestion of the substrates 45 and 74 and prevents untoward effects suchas lodging in the stomach of the substrate or pill itself, as may occurwith non-degradable and smoothly-surfaced polymeric substrates.

The substrates 45 and 74 allow for the placement of a metallic trace forantennae 266, chips 47 and 71, or other electronics via electro-plate,bonding, gluing, adhesive or printing. The antenna 266 may be covered ina protective coating 268 to prevent digestion, protect the antenna fromhandling, and dielectrically isolate the antenna from the enivornment.The paper 82 is superficially coated with the biodegradable substancesuch as polymethyl methacrylate-polymethacryalte, cellulose acetatephthalate, poly lactic acid, poly glycolic acid, various sugars, oils,waxes or proteins.

The biocompatible materials 254 added to the paper also allow forincreased stability of paper materials in more extreme environments,including those of very high temperature and humidity, preventing thetag 15 from warping or deforming (and possibly fracturing the antenna266). Referring to FIG. 6B, the substrate 45 is coated in a multi-layeror patterned method with multiple layers of coatings 254, 264 such thatvarious portions of the tag can be exposed or broken in the body 16 atvarying times or locations. At different times or locations in the body,different coatings may dissolve exposing different types or portions ofthe antenna 266 or sensors to the body 16. These varying conditionsprovide information to the system allowing for determination ofingestion time or tag 15 location. Referring to FIG. 6C, across-sectional side view of an alternate form of the system 260A, thecoatings can be patterned such that different portions of the paper 82are coated with different coatings. This multi-layer or multi-coatedsystem 260A tracks the progress of the substrates as they pass throughthe digestive tract M, E, S, D, I, R or encounter different solutions inthe body 16. In a preferred embodiment, each coating 254, 264 is anEnteric coating that is formulated to dissolve in specific areas of thehuman body 16. In combination with a multi-level electronic sensor andin the form of an electronic pill, the location of the medication istracked through the human body. As each layer of the substrate 254, 264dissolves in its pH or chemically sensitive environment, a newelectronic sensor, which by way of example can be a galvanic cell isexposed. In addition to exposing different sensors or probes indifferent portions of the body 16, the selective dissolution of thecoatings in different parts of the body 16 alters the transmissionproperties of the antenna 266 or system 260A in general, thus making thelocation of the tag 15 in the body detectable without separate sensors.

Various bodily chemicals and even organisms (and their respectivechemicals) can cause the degradation of the materials used with thesystems 260 and 260A. Enzymes, hormones, cells (blood cells), proteins,acids, ions, bacteria, and so forth can contribute to the degradation ofthe substrates or any of the substrate layers.

Furthermore, in another embodiment, the system 10 is triggered todissolve in the patient's body 16 in the presence of both a bodilychemical and an external impulse for additional control. For example,the sensitivity of chemical breakdown is enhanced by the application ofRF energy to the substrates 260, 260A (producing heat or otherwise) froman outside RF source.

The system 10 may also be loaded with various degradation controlchemicals that can delay or hasten degradation rates. This is useful ifthe processing of substrate layers that require extra-thick amounts of acertain layer to be mechanically stable or if a layer requires anotherchemical in addition to the ones found in the human body 16 to begindegrading appreciably.

Antennas and Coatings

Pill or capsules 14 is typically printed with edible inks ofpharmaceutical grade to uniquely identify the product and provideadditional information such as company logo, brand name, and dosageinformation. In accordance with this invention, these edible inks arereplaced with conductive and biocompatible silver inks to pattern smallantennas 266 (FIG. 6A), coils 41 (FIG. 2C) or deposited conductivepattern 44 (FIGS. 5A, 5B) directly on the capsule 14, 17. Othercompositions known in the art are also contemplated such as but notlimited to carbon black, iron, gold, copper, zinc, and conductingpolymers.

Thus, by way of printing, etching, or electroplating, miniature antennae266 are made of silver, carbon black, copper, or other biocompatiblecoatings. Silver, copper, zinc and other metals are substantiallybiologically inert, and when ingested in small amounts, are nontoxic tohumans and pass through the body without being absorbed into tissues.Furthermore, the conductivity of most of these metals is very high,making them excellent conductors. Therefore, the antenna 266 performancenot only depends on physical size constraints, but also on the totalusable concentration of conductive material.

Coatings. Referring again to FIGS. 6A and 6B, it is preferred toencapsulate the components of the tag with a coating 268 for multiplereasons, including but not limited to: electrical isolation from theconductive fluids of the GI-tract M, E, S, D, I, R, prevention ofdissolution or exposure to the body for safety, and selectivedissolution at different locations in the body 16. For example, thecoating 268 prevents contact with the body, limiting exposure of thematerials to the patient 16. Certain coatings can be utilized that arepH or otherwise selectively dissolved in different portions of the GItract. In a preferred embodiment, enteric coatings that do not dissolveuntil they reach the intestine I or other locations, where very littledigestion occurs. This allows the material to break up before excretionbut not leach materials into the blood stream. It is also desirable toactivate the tagging system only after the patient has ingested the pill14. Once ingested, the pill 14 is exposed to stomach acids that eat awaycoatings 268 on the surface of the capsule 17, 46. Coatings 52 (or 268)may be applied or selectively applied to cover parts of the tag orcapsule/pill. In one embodiment, these coatings 268 are appliedselectively to cover certain portions of the tag and capsule but allowother portions of the tag and capsule to break down. This allows the tagto change shape or break down in such a way that it easily passesthrough the digestive tract while still protecting sensitive materialsfrom digestion.

In another embodiment, the conductive layers of the antenna 266 on thetag 15 are made by incorporating a metal that can dissolve, such as ironfilings under a temporary protective layer 268 such as polyglycolic acidor by incorporating particles that are nontoxic by virtue of beingnon-absorbable (e.g., silver or carbon). Degradation of the matrixreleases particles that move through the digestive system of the patient16 without absorption. Such particles are present above a percolationthreshold for conductive “contact” (within 1000 Å), and reside in adegradable matrix such as polylactic/glycolic acid or starch. The degreeof conductivity is adjusted by the degree of close contact and by thenumber of contact points (volume fraction). Particles that are notspherical can be added at lower levels to get good conduction. Hence,graphitic carbon plates can reach a percolation threshold at lowerlevels, and silver can be used as planar particles as well.

In a preferred embodiment, the integrated circuit 47 is encapsulated orcoated in a protective coating such that it is not exposed to the body16 and its digestive process. Packaging preferably does not interferewith the RF communication but provides enough safety for human studies.Methods of use allow access to the aqueous environment for sensors whilestill ensuring safety.

Energy Harvesting

Power sources for body-powered electronic pills must be biocompatible,small in size with the appropriate form factor, capable of deliveringhigh power with good maximum discharge current characteristics and lowself-discharge, and provide long calendar life. Referring to FIG. 4,many techniques exist for harvesting power 205 and storing the power 207within the circuit 47 for use with the tag 15. For example, a simplecapacitor can be used to store the energy at block 207 owing to theshort duration of the active nature of these devices (less than 1minute). The capacitor is embedded into the pill electronics and chargedfrom block 205 by a handheld device via a magnetic field or othermechanism before being swallowed by the patient 16. The capacitor holdsthis charge until activated by a triggering mechanism, such as thedissolving of a specially coated switch by stomach acid.

In one embodiment of the energy harvesting block 205, the chemicalenergy of the stomach contents is converted into electrical energy. Forinstance, the chemical reaction between the stomach acid and a zincelectrode oxidizes the zinc, creating an electric current via a metalelectrode making the return path. In another embodiment, the systemconverts mechanical motion (e.g., peristaltic and other motion common inthe digestive tract) into electrical energy.

In one embodiment, the energy harvesting system 205 harvests the energyof the inlink channel 50, stores the energy in block 207 and uses thisenergy to power the tag 15 and transmit data via the radiative outlink52. Harvesting of the energy from the reader's inlink 50 is sufficientto power the tag 15 and its transmission of the outlink channel 52. In apreferred embodiment, the tag 15 harvests the energy in the inlinksignals 50 until it obtains sufficient energy to transmit a signal tothe external reader 11 along the outlink channel 52. As illustrated inFIG. 15, this harvesting process typically is substantially longer thanthe duration of the burst information sent out by the tag 15, thusallowing for amplification of the outlink channel 52 with respect to theinstantaneous power harvested from the inlink channel 50. For example,if the inlink channel 50 is harvested for 100 ms and the outlink burstof information is 1 ms in duration, the outlink power transmission 52may be 100 times larger than the instantaneous power harvested by thepill 14 from the inlink signal 50.

Ingestion Detection

An important aspect in successful detection of the ingested electronicpills is to positively identify the origin of the transmission, that is,whether the pill 14 is transmitting from inside the patient's body 16.Knowledge of transmission origin is necessary to detect a patient whomight intentionally spoof the system into registering a positivecompliance. Multiple methodologies can be implemented for ingestiondetection with sending element 208. Noting FIG. 17, multiple techniquesexist for “triggering” the system to respond only after reaching thestomach. The trigger can be activated by the dissolving of material thatopens (or closes) a switch. The trigger can be based on electrical,chemical, or mechanical detection of stomach or GI tract contents (e.g.,pH sensor, ISFET, temperature sensor, three electrode electrochemicalcell, MEMS, microfluidics, miniaturized or nanoscale lab-on-a-chip,biomarker targeting, biosensors, optical sensor, sound transducers, bio-or chemi-luminescent sensor, etc.). When spoofing is not an issue, thetrigger can be activated just before ingestion or by the reader 11.Additionally, one also simultaneously measures changes in materialproperties such as physical size (swelling), magnetism,polarizability/polarization, phase (solid-solid, solid-liquid,liquid-liquid, etc.), viscosity, chemical/molecular makeup, opticalclarity, thermal conduction, state of charge and so forth. In oneembodiment, the sensor senses changes in the outer walls of a capsule,such as temperature or conductivity before it comes in contact with theouter environment.

The ingestion detection system using the galvanic gastric sensor 284(FIG. 11) with sensor 208 communicates with the control subsystem 209 ofFIG. 4. The control subsystem 209 is then either programmed to processthe data it receives to determine if the tag 15 is in the properlocation, or passes the data through the transmission subsystem 206 foranalysis by the external components, for example the reader 19 or 111,external device 54, or central database system or healthcare provider60. In another embodiment, the tag 15 does not respond to queries fromthe reader 111 or 19 until the ingestion detection system 208 indicatesthat the tag 15 is in the proper location, such as the stomach S.

Additionally, the presence of specific features in the received signalfrom inside the body may be sufficient to determine the transmissionorigin. For instance, signal strength in outlink 52 coming from insidethe body 16 is lower compared with that from outside the body due toattenuation from tissue, blood, and bones. It is also reasonable toexpect a shift in the resonant frequency or a unique characteristic ofthe frequency spread or content when a signal propagates through tissue,which is absent when the transmission is outside the body 16.

Additional techniques for detecting the origin of the transmission oftag 15 include:

1. The dynamics of pill motion in the esophagus E (e.g., speed of pilltravel, orientation of magnet, and path of travel) and or stomach S mayprovide subtle discriminating differences between the inlink signal 52received from tag 15 inside the body 16 and a tag 15 that is outside thebody. The peristaltic motion of the esophagus and the tossing andturning in the stomach may produce pill motion that affects the signalsreceived due to the natural or purposely modified directionality of thefields generated by tag transmission. Additionally, there is a normalprogression from mouth M to esophagus E to stomach S that will produce adifference in motions that must be obtained sequentially to validate thelocation of the pill 14.

2. Transmission of unique codes based on a variety of potential sensorsattached to the tag 15. In one embodiment, body temperature and/or pHsensors are included in the ingestion detection system 208 and eitherprocessed or relayed by the control system 209 to the transmissionsubsystem 206. The control subsystem 209 can transmit either raw sensorback to the reader 111 or 19 for analysis of the patterns, or processthe data itself and transmit back to the reader 19 (FIG. 1) or 111 (FIG.3) an indication of its location.

3. Ensuring that the pill 14 is only active inside the patient's body16. For instance, the pill 14 is inert when dispensed and is activatedupon contact with saliva and/or other bodily agent.

4. Alternatively, the pill 14 is activated outside the body 16, prior toingestion, and deactivated inside the body 16 after coming in contactwith bodily fluid.

The activation/deactivation process can be carried out using, forexample:

1. Selectively coated sensors that exhibit change in properties in thepresence of specific chemical compounds.

2. Biodegradable switches based on proteins that are broken down whenexposed to digestive enzymes in the stomach.

3. Unique GI fluid sensors based on the properties of the GI fluid.

Conductive sensors. One implementation strategy of a bio-switch is tointerface the conductive sensor with a transistor (e.g., MOSFET, FET,BJT, etc.), as shown in FIG. 7. A conducting sensor in series withresistor R1 acts as a simple resistor divider and provides the necessarybiasing voltage to the transistor gate. The output of the bio-switch istaken from the transistor drain and fed to the enable port of the RFtransmitter (an RF transmitter is used as an example, but can be anyelectronic device that requires activation). A power source providesnecessary power to drive the transistor and activation voltage. When thebio-switch is outside the body, the resistance of the conductive sensoris small compared to R1; thus the activation voltage (VA) will be belowthe gate threshold voltage. When the gate voltage is below thethreshold, the transistor is turned off and the voltage at output equalszero. When the bio-switch comes in contact with a bodily fluid, selectchemical molecules will bind to the conductive sensor and increase itsresistance, thereby also increasing the activation voltage. When theactivation voltage increases beyond the gate threshold voltage, thetransistor turns on, and voltage at output equals that of the battery. Alarge voltage at the output in turn enables the RF transmitter andreadies it for transmission.

An alternative implementation is shown in FIG. 8, where the circuitconfiguration yields a deactivation circuit. When the bio-switch isoutside the body, the voltage at output equals that of the battery; thatis, the RF transmitter is enabled. When the conductive sensor comes incontact with a bodily fluid, the transistor is turned on and voltage atoutput equals zero, thereby disabling the RF transmitter.

A bio-switch implementation using a conductive sensor is not limited tothe above examples. Variations in transistor type, substrate type,biasing schemes, selection of power, etc., can yield several differentimplementation options. An exemplary concept here is the utilization ofa conductive sensor to drive a switching mechanism. In the aboveexamples a battery was used to drive the transistor and circuitry, butinstead a charged capacitor can easily replace the battery. The switchcan also be used to modify the frequency of the signal transmitted ordetected externally (e.g., changing the frequency response of thepill/antenna). The capacitor can be charged before a pill is dispensedor can be charged by RF induction as is done in RFID techniques. Onepositive aspect of using a capacitor is that over time the capacitorwill discharge and the entire system will become inert, meaning thesubject must take the pill within a given time frame, thereby increasingthe robustness of the system to spoofing.

MOSFET sensor. Another implementation of the bio-switch is to use aMOSFET e-nose sensor instead of a conductive sensor. A bio-switch with aMOSFET e-nose sensor can be implemented with much simpler supportingcircuitry since the transistor does both sensing and switching. Anexample is shown in FIG. 9. The resistor divider of R1 and R2 provides afixed activation voltage to the transistor gate. When the bio-switch isoutside the body, the activation voltage is just below the gatethreshold voltage; therefore, the transistor is off. When the MOSFETsensor comes in contact with a body fluid, a catalytic reaction takesplace at the transistor gate and changes the channel conductivity; i.e.,the gate threshold voltage is lowered so that the activation voltage isnow above the threshold voltage. Therefore, the transistor turns on, andthe voltage at output equals that of the battery. Again, thisillustration is just one possible implementation scheme, and variationscan be constructed with different types of substrate (e.g., n-type andp-type) and supporting circuitry.

An additional embodiment utilizes biodegradable switches that undergosignificant changes in conductivity when exposed to the digestiveenzymes of the stomach. One can mix a conductive substance (e.g.,carbon) with a non-conductive substance (e.g., protein). A conductivesubstance doped with a non-conductive substance will tend to have lowerconductivity (high resistance) than a pure or even semi-doped material.When the doped material comes in contact with digestive enzymes, thenon-conducting material is broken down or dissolved by the enzymes,leaving behind just the conductive material. One possible switchimplementation can be based on a composition of carbon and albumin. Thealbumin protein is broken down by pepsin, an enzyme that is naturallypresent in the stomach. When the switch composition is devoid ofalbumin, the conductivity of the switch increases and bridges a gap inthe circuit to complete the circuit. A number of possibilities exist inselecting a conducting material and a protein. Furthermore, it is alsopossible to incorporate multiple non-conducting materials to yieldswitches that are extremely selective to activation.

In the embodiment shown in FIG. 4, the in-link 50 signal is used forenergy harvesting 205 and the in-link signal 50 is sufficiently low infrequency such that most of the energy is transferred galvanicallythrough the body of the patient 11, the tag 15 is only easily poweredwhen the tag 15 is in contact with the body of the patient 11 since thein-link signal is significantly attenuated in the air. As such, the tag15 will not respond to queries from the reader 11 until such time as thepill is being touched or ingested by the patient 11. This provides alevel of spoofing prevention with virtually no additional complexityadded to the system.

Noting FIGS. 10A and 10B, in order to ensure that the pill is ingested,the antenna system can be disabled by electrically “shorting” theantenna through the use of an ingestible switch 90 that contains acircuit breaker 92 that becomes modified in the presence of gastricjuice. An embodiment of this concept includes a method of breaking acircuit via the swelling of the breaker material in the presence ofstomach fluid. The switch 90 comprises a thin layer of hydrogel 92partially coated with a conductive trace 94 such as metal flake ormicro-thin metal foil. When the hydrogel is exposed to low pH liquid, itswells to about sixteen times its normal size and breaks the conductivetrace 94. This mixture is then coated with an albumin-based layer thatwill prevent exposure of the hydrogel to fluids until the albumin isselectively broken down in the GI tract by either pepsin or typsin. Thepreferred mechanism for deactivating the system using an ingestibleswitch 90 is to electrically connect the two pads of an antenna 13,creating an electrical “short”. The lower the resistance, the more poweris diverted from the signaling antenna. By way of example, a five ohmresistance is sufficient to reduce the input power from the antenna by95+%. A resistance of 10K ohms will reduce the input power to thesignaling chip by only 10% or less. In the case where the in-link 50 isseparate from the out-link 52, either antenna can be shorted by thistechnique, essentially crippling the tag 15. The preferred embodiment isto short the in-link antenna in a system that utilizes the in-link topower the system.

Sensor such as pH sensors and other chemical sensors are fairly complexdevices. Noting FIG. 11, to avoid a requirement to embed such a complexdevice into the tag 15 or integrated circuit 20, the preferredembodiment of a gastric sensor 208 utilizes a galvanic couple 208 thatis placed in various bodily fluids (stomach fluid, esophageal fluid, GIfluid, etc.) to create a measurable change in electrical properties suchas current, voltage, and/or resistance and allow digestible electronicsto evaluate the location of a tag 15 in the human body 16. In oneembodiment, the sensor 208 senses changes in the out walls of a pill 14,such as temperature or conductivity before it comes in contact with theouter environment. In the preferred embodiment, the galvanic couple canprovide discrimination of location as well as providing electrical powerto the system. The ingestion detection system 208 on the tag 15 workseither outside or inside a pill 14. Inside the pill, the detectionsystem 208 operates when the GI fluids permeate the pill or dissolve anyexternal layers. The tag 15 begins generating power and voltage as soonas it is wetted by ingestion and allows the tag 15 to begincommunicating with the reader 111. As the tag moves through the GI tractM, E, S, D, I, R, the sensor or voltage information is communicated orprocessed by the control logic 209 such that location information can bedetermined by the reader 111 or other external system. FIG. 11 shows theGI sensor/energy cell connected to control logic 208. The GI sensorrequires two electrodes for operation and one or both of theseelectrodes may also function as antennas. In the preferred embodiment,one of the electrodes for the GI sensor comprises a small strip ofmetallic zinc while the second electrode consists of a specially coatedsilver electrode that is shared with the inlink antenna.

In one embodiment, the galvanic couple 284 is constructed of twodiffering metals 280, 282 or compounds that, when placed in a bath ofany number of solutions, produces an electric voltage and subsequentcurrent and is measured by the control system 208. Metals used for agalvanic gastric sensor 284 are transformed by a number of chemicalreactions to produce a new chemical compound. The new compound changesthe differential voltage. Upon immersion in a target fluid, the compoundtransforms into a different compound and accompanying the transformationis a change in voltage. Other changes in the galvanic cell materials canbe phase transitions, state transitions, amount of the chemical compound(causing a natural change in differential voltage based on the degree ofmaterial available to sustain such a voltage), and other materialstransitions that cause a change in the electrical output of the galvaniccell. In the preferred embodiment, the GI sensor creates varying degreesof current or voltage depending on the nature of the fluids in which itis immersed. Thus, the GI sensor not only gives true/false data aboutthe environment, but may also senses thechemical/electrical/thermal/etc. makeup of the environment and give asignal corresponding to the state.

The metals or compounds are connected to a measurement means in thecontrol logic 208 (FIG. 11) and can be a voltmeter,potentiostat/galvanostat, electronic switch or other means to measure orgauge the voltage and report if and/or when the target electronicreading is reached in the target solution. If the sensor 284 is not inthe target solution, the voltage will not change appreciably as nochemical transformation will proceed. Thus, the voltages or an indicatorof location can be transmitted via the tag 15 to the reader 11 or 111 toconfirm the location of the pill 14. Such chemicals transformationsinclude silver phosphate and other silver compounds, including silverchloride, silver sulfate, silver carbonate, or even silver metal itself.Transformation can occur on the anode or cathode of the galvanic cell.In the preferred embodiment of FIG. 11, a silver phosphate electrode 280is attached to a zinc electrode 282, and the silver phosphate transformsto silver chloride and silver metal while the zinc oxidizes to zincmetal or forms a zinc compound with anions in solution. Accompanying thesilver materials transformation is a voltage differential (fromhigh-to-low or low-to-high state). The voltage/current differential isaffected by the selection of the two metals or compounds (or mixthereof), whereby a silver phosphate-zinc system differs in outputvoltage/current from that of a silver-phosphate-copper or silversulfate-zinc system. Furthermore, a dissolvable or protective coating281, 283 may be applied to the electrodes 280, 282 such that theelectrodes are not exposed to the fluid until a certain externalcondition exists, such as when the tag 15 is exposed to the highchlorine content of the stomach. Coatings on each electrode 281, 283 canbe the same or different, providing flexibility in the voltages andcurrents produced in different transit times and locations in the body16.

FIG. 12 is a chart describing the voltages measured from the silverphosphate electrode 280 of FIG. 11 formed by applying 9V to a silverchloride electrode in KH2PO4 solution with a silver electrode returnpath 282. The silver phosphate electrode 280 was tested at loads of 20kOhm and 1 kOhm. The charts in FIGS. 12A, 12B and 12C show the timecourse of voltages of the electrodes with differing amounts of phosphate(exposure time to the KH2PO4 solution), differing loads, and differingsolutions. The gastric sensor 284 has a substantially different voltagein HC1, the primary component of stomach fluid, versus sulfuric acidsolution.

In alternate embodiments, the tag 15 is modified to include sensors toprovide the ability to access the tag's internal memory. For instance,the tag 15 can have a pH monitor, temperature probe, or other sensors 42(FIG. 2C) to verify compliance. In addition, it may be beneficial to usea system that can also provide a readout of the signal strength. Thissignal strength is beneficial for optimizing the communication protocoldynamically as well as providing potentially discriminating informationrelating to the location of the tag 15.

Biometrics

In addition to determining when the pill 14 is ingested and where itresides, it is important to detect that the pill is ingested by theappropriate person. As such, a variety of biometrics are utilized todetect that the reader 111 and/or pill 14 are located on or in thecorrect person 16.

In one embodiment, an electronic pill monitors physiologic signalsinside the body 16 that are typically difficult to mimic outside thebody. For example, the patient's electrocardiogram (ECG) is detected andmeasured by the electrical contacts or antenna of the tag 15. The tag 15either processes the signal or passes the signal via the outlink 52 tothe reader 11 for further processing. Detecting the presence of a validECG signal indicates that the tag 15 is inside the body 11. Detection ofa periodic pulse between 30 and 120 BPM is sufficient to detect that thetag 15 is inside the body. Furthermore, a wide variety of parameters canbe extracted from the physiologic signals detectable inside the body 16.In a preferred embodiment, the processing system (either in the tag 15,reader 11, or elsewhere downstream) detects parameters of the electricalcharacteristics of signals received inside the body 16 including but notlimited to: periodicity, amplitude, signal shape (including peakgeometry, relative height), and signal to noise ratio. In addition, thesignal detected inside the body can be transmitted to the reader 11 andverified against a preloaded signature of the ECG or other physiologicsignal recorded earlier, for example, during the initial administrationof the system 10. Additionally, the reader 11 can record the same signaloutside the body 16 and ensure that the tag 15 is in the same person 11that is wearing the reader and also checked against the storedsignature. These features of the ECG and other physiologic signalsmeasured at the tag 15 or reader 11 are also capable of biometricidentification.

These physiologic features and their dynamic features (changes in thesignals over time) are useful to identify the patient 16, ensureingestion, or determine the location of the tag 15 in the digestivetract M, E, S, D, I, R. The dynamic features include but are not limitedto heart rate variability, changes in signal strength as the tag movesthrough the body 16 and muscle activity in different parts of the body.For example, the ECG will be quite strong as the pill passes the heartin the esophagus E and then gradually get weaker as it moves fartherfrom the heart in the GI tract S, D, I, R.

In an embodiment, the external reader 11 is used to monitor and assess agiven patient's 16 ECG output (periodicity, peak geometry). Thisinformation is used for a first calibration step and recorded as thebaseline ECG output. The later measurement of the ECG by the reader 11validates that the same person is using the reader. Additional, themeasurement by the tag 15 can be checked against this calibration toensure that the proper person is taking the medication. In this case, ifeither the medication or the external reader is switched to a differentperson 16, the results can be checked against the calibration data.Calibration can take place in the presence of proper supervisingpersonnel, including doctors, nurses, etc., and the calibration can belocked to those who either have calibration codes or calibrationdevices.

These biometric capabilities can also be used to help guard againstimproper medication (type or dose) being taken. Each tag 15 can beprogrammed to be taken by a specific patient. The patient specificitywill be recorded by certain physiologic signals that can identifyindividual patients, such as parameters of the ECG. The reader 11 orinterface 54 can first be programmed to register the kind and frequencyof medication to be taken for a given patient ECG. The reader 11 orinterface 54 then alerts the patient or proper personnel if themedication taken was given to the wrong person (pill ECG does not matchreader ECG) or if the medication was taken at improper time intervals(over-or under-medication).

Control Logic/Ic Design

Maximizing power efficiency is of utmost importance to maximize thereading distance between the reader 11 and the tag 15 as well as poweroutput and detectability. Advanced low-voltage and low-power circuitdesign topologies and a suitable process technology are required toachieve operation with small input power levels from radiatedelectromagnetic fields.

Referring to FIG. 13, the preferred embodiment of the integrated circuit20 for the tag 15 includes: protocol logic 306 having a random bitgenerator XXX for robust two-way communication and control, dataacquisition subsystem 304 and sensor 314 to determine the strength ofthe in-link signal 50, inlink subsystem 302, outlink subsystem 308, andenergy harvesting and storage system 310. The IC 20 is designed withfallback operating modes, including a chirp mode and a beacon mode. Inthe chirp mode, the protocol is suspended and the IC 20 transmits datawhenever it has sufficient power from the energy harvesting and storagesystem 310. In beacon mode, the IC 20 transmits a periodic burst patternwith no data (bypassing all digital logic). In one embodiment, theenergy harvesting and storage system 310 extracts power from inducedcurrents generated from the external reader 11 via the inlink subsystem302 or directly via the inlink antennas 50. In a second embodiment, agalvanic cell, GI sensor, thermocouple, or other method of generatingpower from the digestive tract M, E, S, D, I, R or motion through itprovides primary or supplemental power via the energy harvestingsubsystem 310 to enable the IC 20. The outlink subsystem 308 drives theoutlink signal 52 under control of the protocol logic and controlsubsystem 306. The protocol and control system 306 contains all thelogic to control the IC, the communications protocol, the dataacquisition, synchronization, and data storage and output, including thepreprogrammed information about the medication, patient, study and otherinformation. Minimizing the power usage of all these subsystems and inparticular the outlink subsystem 308 is of utmost importance.

Preferably, the IC 20 is fabricated using industry standard CMOSmanufacturing processes in class 10 or better clean rooms. The physicaldimensions of the IC 20 are expected to be very small, less than 1 mm×1mm×0.1 mm. When affixed to the tag 15, the IC 20 is encapsulated inbiocompatible epoxy to cover any hard edges and to prevent interactionbetween the IC 20 and the patient's body 16. The preferred IC 20 is acustom designed microchip that stores the medication information, readsthe GI sensor, and implements the signaling and communications protocol.The IC is designed to operate with extremely low power and to providereliable deep in vivo communications.

In addition to integrated circuit implementations for the various logicand systems of the tag 15, another embodiment includes printedelectronic circuits created with various inks including metallic,dielectric, and organic materials. The creation of complex printedelectronics requires the creation of multilayer electronic devices suchas transistors and capacitors, silver conductive ink and dielectricmaterials are typically loaded into separate ink cartridges. Forexample, In the case of capacitors, fabrication can be achieved by firstprinting a single line of nanoparticles onto a substrate that is heateduntil the inks are metalized. Next, a dielectric of polymer is printeddirectly over the line. Finally, a second conductive line is printedperpendicular to the original conductive line. In this way, theoverlapping cross-section of the two conductive lines—with a dielectricbetween them—creates a capacitor whose capacitance is defined by theoverlap area and the dielectric material and thickness Thus, if anantenna is printed simultaneously and attached to each conductive line,a simple 3-step inking procedure is enough to begin creating simpleinductor-capacitor antennas that can resonate at a tuned frequency.

Many generally recognized as safe (GRAS) materials are available for useas dielectrics, for example polytetrafluoroethylene (PTFE), polyimide(from precursors) and PVP. In the preferred embodiment, enteric coatingsare used as a dielectric material.

Communication Links and Protocol

Transponder Antenna Size and Efficiency. The radiation efficiency of atypical loop antenna increases with loop area and is inverselyproportional to the excitation signal wavelength. Since the loop area islimited, it is desirable to operate at higher frequencies to improve theantenna efficiency. In typical RF applications, operating at higherfrequencies can improve the aperture efficiencies of small antennae tomaximize the received power. However, in biological systems, theoperating frequency is a tradeoff between increased path loss in tissueand antenna efficiency. Indeed, RF signal attenuation behavior of theinlink 50 and outlink 52 in bodily fluids and body tissue to and from aningested tag 15 is complex and difficult to model.

The tag 15 may be coded with a variety of information including but notlimited to data about medication, the patient 16, the reader 11, or thedrug trial the patient is participating in. Additionally, the tag 15 canhave a unique ID that is utilized with a database of other informationtagged to each tag ID to obtain similar information without storing iton the tag 15. Upon detecting the tag 15, any of the readers 11, 111,211 or 311 can store a time-stamped reading of a medication event. Ifthe tag 15 is not detected, failed compliance can be signaled, forexample, to the patient 16 and/or to a second party such as a healthcare provider or other agency 54 via input and output signals 56, 58.

It is preferred that the communication between each reader 11, 111, 211or 311 and the tag 15 provides two way communication, with thecommunication from the reader 11 to the tag 15 being preferably througha conductive in-link channel 50 and the communication from the tag 15 tothe reader being preferably through a radiative out-link channel 52. Thein-link channel 50 is preferentially in the range of 1-20 MHz; thisfrequency range produces efficient data transfer from outside the bodyto deep inside the body 16 and can travel through the body galvanically,requiring very small antennas or pads only to receive the signal.Because the inlink transmissions 50 travel galvanically, the signalingattenuates very rapidly outside the body 16 thus providing for increasedprivacy for the inlink channel 50. Skin surface contacts with thereader, as readers 111, 211 and 311, maximizes the efficiency of thein-link transmission 50 from the reader. The in-link channel 50communicates a variety of information to the tag 15, including but notlimited to querying for the presence of the tag 15, turning the tag'stransmitter on or off, collision avoidance, and various otherprotocol-based communications. The inlink channel 50 also providessynchronization signals between the reader and tag 15. Synchronizationbetween the reader 11 and tag 15 are particularly important when theoutlink signal 52 is very small (as is expected when coming from insidethe body) and/or when the outlink signal is transmitted in very shortbursts for better energy efficiency.

In an embodiment, the tag 15 is powered using the RF energy received byits coil or antenna or in another embodiment where power is generated byenergy harvesting means. As described previously, this power can bestored temporarily and then used to transmit a pulse or signal to thereader 11. Storing the energy internally in the tag 15 helps alleviatetwo distinct problems. First, it allows for the storage andamplification of the instantaneous power received from the inlink 50 orenergy input 312 to create higher powered but shorter bursts of outlinktransmissions 52. Second, when transmitting into the body 16, theexternal powering signal (inlink 50) creates significant noise that maymake detection of the outlink signal 52 from the tag 15 very difficult.

One method to create more detectable signals for outlink 52 is toutilize different frequencies for power transmission and data signaling.This allows the external receiver 12 of the reader 11 to befrequency-isolated from its transmitter. A frequency selective filtermay then remove the noise from the transmitter to allow for high qualityreception of the data signal. Lower frequency signals typically havelower losses in the human body. As such, the power transmission signal50 may necessarily be lower in frequency than the data transmissionsignal 52 which can be much lower in power.

Another method involves the use of dual antennas on one or both of thetag 15 and receiver 12; that is one antenna or set of probes/contactsfor the transmission/reception of the in-link or power transmission, theother for transmission/reception of the data signal.

As discussed in greater detail below with reference to FIGS. 15-18,another method involves the time multiplexing of the signals such thatthe power transmission ceases during predefined time periods to allowtag 15 to start transmitting data. The circuitry of tag 15 can bedesigned to utilize this cessation of power transmission as a marker todetermine when to start transmitting data. Additionally, that circuitrymay store the power during the “power cycle” for a period of timetypically longer than the transmission cycle to provide a powermultiplication to improve the signal strength of the data transmission.

It is preferred that the communications to and from the tag 15 and toand from the readers 11, 111, . . . are protected, encrypted, encoded,or made secure in a way to prevent interpretation by other devices andhave software and/or hardware required to protect the data and supportprivacy or data security requirements of the communication system.

Although the technology described above focuses on RF technology, manyother technologies are possible. The passive devices that are detectedvia an external sensor can include many standard imaging technologiessuch as X-ray, ultra-wide-bandwidth (UWB) imaging, ultrasound, or MRIdevices. Each can have a transmitter that transmits energy into the bodyand detects reflections or distortions in the magnetic field caused bythe presence of the pill (or pill contents or coating).

Many of the tag 15 embodiments support IDs and other stored data thatcan be transmitted back to the reader 11 via the outlink channel 52. IDsand other data can be transmitted via pulsatile signals (information inthe pulse duration, pulse spacing, pulse frequency, etc.) or via digitalencoding. To increase signal-to-noise ratio, it is preferable to have atransmit/receive event wherein the tag 15 responds to a request from thereader 11 with a predetermined signal. This signal is repeated and thensynchronously averaged over multiple transmit/receive events to producea better signal-to-noise ratio. Synchronization of the transmissionsfrom and to the reader 11 and tag 15 also improves the ability of thereader 11 to detect faint signals 52 from the tag 15 in the body 16.

An embodiment of an efficient communication and protocol approach isdemonstrated in FIG. 14. The approach is based on a unique communicationpath between the tag 15 and the associated reader 11. The reader 11transmits data to the tag 15 by way of the conductive or galvanicin-link 50 communication channel. The tag 15 transmits data to thereader 11 through the out-link radiative channel 52. An electromagnetictransmitter block 320 provides the interface to the radiative channel 52at the tag 15 and a corresponding reader RX 322 extracts the signal atthe reader 11. A tag 15 for a patient 16 is linked directly to thepatient reader 11 similar to a key and lock. Only data with the properkey or data word are recognized by the reader 11 as valid patient data.As an extra measure of protection, the out-link TX carrier 320 is phaselocked to the reader in-link signal 50 to provide means forsynchronization of data. Phase lock also allows coherent detection ofthe tag data at the reader 11, thereby enabling use of phase modulationand reduced error rates. Since the in-link signal 50 is propagated bydirect body contact (in-link conductive channel), only the reader 11attached to the patient's body 16 can properly demodulate the return tagoutlink 52 data. This feature makes external eavesdropping of the datavery difficult. Hence, this approach enhances security of the data. Aswill be appreciated, this communication protocol also allows severaltags to be consumed and data read without the need for individual tagidentification bits, thus reducing significantly the amount of data thatneeds to be stored.

The protocol is composed of the communication link timing and theassociated in-link 50 and out-link 52 data fields. FIG. 15 depicts therelative communication link timing of the data for the in-link 50 andout-link 52. The process begins with the reader 11 sending an FMmodulated signal, or “in-link header” 330 to the tag 15 with informationnecessary for proper tag operation. The header is sent periodicallyevery T seconds. On ingestion, a random bit generator in the circuit 20for the tag 15 begins operation. On completion of the in-link headerfield 330, the value of the random bit generator is latched. Thislatched value is used to set the time, t₀ at which the tag 15 respondsto the reader 11 by sending a data burst 332. The data burst 332contains a subset of the data stored on the tag 15 to be sent to thereader 11. Several bursts 332 in sequence make up the full datatransmission through out-link 52. The latched random generator valuebecomes the pill ID or address for this specific tag. Since the ID israndom, each tag swallowed will have a unique ID. As will be appreciatedby those skilled in the art, the algorithm may be as simple or complexas necessary to assure no two tags randomly end up with the sameaddress. Each tag swallowed will send a pulse 332 delayed in time fromthe end of the header 330 proportional to the value of the randomaddress. In this fashion, no two tags 15 can transmit at the same time,thus preventing interference but also allowing multiple ingestion oftags. Also, since the tag address is set randomly, there is less needfor special tag identification bits to be stored on each tag, thusreducing significantly the number of bits of memory required on the tag15. This reduces cost and complexity of the tag 15 significantly.

Referring to FIG. 16, a representative efficient inlink data field 342and corresponding definitions are shown. Field selection can be used toimprove the robustness of the communications between the reader 11 andthe tag 15. For example, the field N defines the number of data bursts332 that the tag 15 uses to define a single tag information bit. Thus,it is appropriate to use a mechanism by which the system 10 assigns moredata bursts 332 per bit for situations where the signal to noise ratiomay be poor (very large patients for example). This allows for moreintegration time and improved reliability. Such a system is adaptablefor broader utility.

Referring to FIG. 17, a representative efficient outlink data field 352is configured to allot two data bursts 332 for a single bit 354.Depending on the total number of bits J of information transmitted, N×Jdata bursts are generated. For example, if the total number of bits 354is J=16 and N=2, then 32 data bursts 332 are transmitted. As a furtherexample of the utility of this protocol, the reader 11 may bepreprogrammed to only accept outlink data with the proper patient ID.This along with the fact that the data is coherently linked to thereader 11 essentially reduces the likelihood of data not associated withthis patient 16 being received as valid data.

FIG. 18 shows the timing for the case of three tags taken together tofurther illustrate the efficiency of the protocol. Tag 1 362 transmitsat a random slot after the inlink header 330 and transmits multiplebursts 332 per bit 354. Similarly, Tag 2 364 and Tag 3 366 transmittheir multiburst per bit transmission in different time slots after theinlink header 330.

As has been previously discussed, a communication network utilizing aphase based modulation scheme is known to have advantages of reduced biterror rate (BER) for the same transmission power compared to simplemodulation schemes such as Amplitude Shift Keying (ASK). Since power isextremely limited in in-vivo communication systems, minimizing BER is achallenge. Implementing a phase-based modulation scheme requires thatthe reader 11 be able to coherently demodulate the signal 52 for eachtag 15. This normally requires that the frequency stability of each tag15 be within a tight tolerance (20-40 ppm) to permit the reader 11 tophase lock and demodulate the received signal. Such frequency tolerancerequires that the tag 15 transmit frequency be based on a crystalreference. Size and safety constraints prohibit the use of crystals togenerate the transmit signal for the tag 15. Further, since the tagtransmission burst is short in duration, there may be issues in propersettling which may cause demodulation errors. Another solution is forthe reader 11 to have an independent receiver for each tag 15 andpreferably use a phase lock loop based approach to lock to the incomingsignal. There are issues with this approach as well. First, the burstdurations are short making the design of such a receiver extremelydifficult. Second, the tag 15 still requires some measure of frequencytolerance to assure regulatory or system specifications are achieved.This may require the need for tag frequency trimming which adds to themanufacturing and test costs of each tag 15. Hence, a method is requiredto eliminate the need for a tight frequency tolerance on the tag 15 aswell as a complex reader 11 receiver design.

A preferred approach takes advantage of the fact that the reader 11 isconnected via the conductive inlink 50 communication channel to each tag15. Hence, by using the reader 11 as the initial frequency reference andlocking each tag 15 to the reference signal for reader 11, aself-synchronized coherent communication system is realized. FIG. 19illustrates this concept in detail. First, the reader 11 generates areference signal (shown here for example with frequency of 4 MHz). Thissignal is passed to the conductive channel 50 through an interfacecircuit 372 and propagated to any tag 15 within the channel. At the sametime, the 4 MHz reference 376 is frequency multiplied within the reader11 to the tag 15 burst frequency (400 MHz by way of example). Thissignal is ultimately used to coherently demodulate data from any tag 15.In the tag 15, the 4 MHz reference frequency is extracted, amplified andpassed to the input of a PLL demodulator and TX carrier generationcircuit (TAG PLL) 374. This circuit has several modes of operationincluding the tag burst mode. During the tag burst mode, the signal isfrequency multiplied to the TX frequency of 400 MHz. This signal issubsequently passed through the outlink 52 channel where it is extractedat the reader 11. The reader local oscillator 378 derived from theoriginal 4 MHz reference is used to demodulate the received tag signal52. The system is self coherent. Thus, the tag 15 achieves a tighttransmission frequency tolerance by virtue of the phase lock loop 374and does not require any internal crystal reference.

Other advantages of this embodiment may be seen by referring to FIG. 20.This figure shows the timing relationship between the inlink 50 andoutlink 52 burst signal and defines the three modes of operation of theTAG PLL 374 network. The inlink data is sent at a periodic rate of Tseconds, typically on the order of 1 ms. As described earlier, the tag15 responds some time later (less than 1 ms) with a TX burst. The TXburst also repeats at the same 1 ms interval. A single period isexpanded in FIG. 20 to further highlight the modes of operation of theTAG PLL. The TAG PLL operates continuously. During mode 0 382, thereader sends a fixed reference signal of frequency Fref (4 MHz). The TAGPLL locks to this frequency and remains locked until progressing to mode1 384. During mode 1, the TAG PLL remains locked; also during mode 1,the reader 11 frequency modulates the 4 MHz reference signal with anyrequired information or configuration data for the tag 15. Since the TAGPLL is still locked to the reader signal, the modulated data candirectly be extracted from the VCO control voltage 375 on the TAG PLL.Hence, during mode 1 384, the TAG PLL is acting as a demodulation block.The TAG PLL then returns to mode 0 382 and stabilizes. Finally, duringmode 2 386, the PLL is given the command to frequency multiply the 4 MHzreference signal, generating the 400 MHz TX burst signal. This is anefficient realization using the same circuitry for both inlinkdemodulation and TX carrier generation.

FIG. 21 shows more detail of the TAG PLL 374. One key to its operationis the dual frequency VCO 392. During modes 0 and 1, the VCO 392operates at 4 MHz. During mode 2 the VCO 392 is switched to 400 MHz(with VCO gain parameters changed accordingly) at the same time a divideby N (100 for this example) is enabled within the loop. The frequency ofthe phase detector 394 remains unchanged and the loop dynamics remainthe same. As a result the loop quickly settles to a precise 400 MHz andthe TX burst is transmitted. Once the TX burst 332 is sent, the PLL 374is returned to mode 0 and the process repeats.

It will be appreciated by those skilled in the art that thisimplementation has several advantages. Using fine lithography integratedcircuit technology, the power requirements for the VCO 392 during mode 0and 1 are very minimal. Simple ring oscillator approaches may be usedfor the VCO 392 requiring just a few micro-amps of current. This allowsthe TAG PLL 374 to operate continuously which then permits a veryfrequency tolerant transmission burst. The TAG PLL 374 will stabilizewith each subsequent burst. The same circuitry is used for both transmitand receive and area requirements are very small leading to a low costsolution.

Attachment (Inside, Outside, Both; Premade Built in, Attached)

Wrapped tag embodiments are shown in FIGS. 5A and 5B. Noting FIG. 5B,the wrapping process is typically partially around or completely aroundthe outer surface of capsule 46, soft gelcap, or other medicationcarrying device as shown in FIG. 5B. The resent invention also includesthe method of attaching the tag 43 to the inside surface of the capsule46 as shown in FIG. 5A.

Referring again to FIG. 5B, to avoid the accidental or purposefulremoval of the tag 43 from the outside of the capsule 46, avoid damageto the tag from handling and environmental issues and to increase theaesthetic appeal of capsules (and minimize patient hesitation in takingan electronically-tagged medication), it is prudent to conceal allelectronic devices, including antenna 44 and chip 47, inside an opaqueor mostly opaque gelatin capsule while maintaining communications tovarious body-dependent sensors or electronic devices. Inconspicuousleads that lay flat on the surface of the gelatin capsule 46 are likelyto be of little indication of the presence of a more complexantenna-chip structure within the capsule 46.

Now noting FIG. 5A, further placing the tag 43 inside the capsule 46maintains a minimal change in capsule volume, and simplifies tagattachment and functionality. Referring to FIGS. 22 and 23, a trace orfoil 49 that runs from inside the gelatin capsule to its exterior allowsfor electronic transmission from within a capsule or power harvestingfrom outside the capsule. The exposed antennas or leads 79, 44, 81 onthe tag 43 make electrical contact with the interior-exterior lead 49 onthe capsule 43. The interior-exterior lead 49 is preferably constructedsuch that an elongated pads 86, 87 are included to make contact with theantennas or leads 79, 44, 81 of the tag 43. The tags are constructedwith coatings such that only the leads or antennas that need to beconnected to the interior-exterior leads are exposed while all otherelectrical components and antennas are coated in a protective and/ordielectric substance. To make the interior-exterior connection, themetal film 49 is thin enough to allow a 2-part gelatin capsule to stillsnap together, The tag 43 itself, being composed only of thin components(antenna, chip, substrate, etc.), takes up a minimal amount of volumewithin the capsule 46 and should not impair drug loading amounts.

When the pill 14 is in the form of capsule 17, an alternative method isto place the tag 15 inside the capsule and allow the tag to worknormally after the capsule begins to absorb fluids. A tag 15 using leadsthat make contact with the interior wall of the gelatin capsule 17 andactivate upon wetting of the capsule can react with the environment toidentify location, chemistry, or otherwise. The system 10 can then usethe gelatin capsule itself as a protective system in non-aqueousenvironments. The diffusion time of fluid through the capsule wall isthe limiting factor for detection of body fluids ortransmission/reception of signal within the body itself. To make contactwith the outside environment in an expedient manner, however, thereceiving pads must be in direct contact with the capsule as some pillssimply swell outwardly. Thus, for this approach an adhesive forattaching the tag 15 to the inside wall of the capsule 17 is required.This will help prevent tampering, prevent misfiring of the pill 14 inbeverages or other liquids, or other problems with proper antennafunction as there are no external leads whatsoever. Destruction of thepill 14 and its contents is then necessary to access any electronics.

In most cases, placing the tag 15 inside the capsule works well. In somecases, the delay between ingestion and activation of the sensor systemon the tag 15 when using a gastro-intestinal powering system may beproblematic. Fitting the tag 15 with external exposed sensor or padswould be advantageous for quick analysis of the body environment foradvanced location discernment. Transit from mouth to stomach typicallytakes place in less than 8 seconds, which is faster than most gelatincapsules can absorb fluid and begin to break down. Having an externallead minimizes this delay in sensing time for an internally-placed tag14. The number of pads that need to be exposed can be as few as one,depending on configuration.

Noting FIG. 23, in one embodiment, the tag 43 has a chip 47 with a highfrequency antenna 47 and a low frequency antenna 79, both deposited on abiocompatible substrate 45 that fits inside a gelatin capsule 17. Leads78 on the antenna 72, 73 are exposed to make contact with the externalpads 80 surrounding the capsule 76. This embodiment also allows for“hot-swapping” of internal and external components of the tag 70.Different geometric designs of an external antenna can be accommodatedby an internal tag by creating a system that simply needs “lining up” ofantennas with external traces. This way, a number of antennas/sensorprobes can be produced that have specific applications (frequency, powertransmission properties, size, complexity) for a specific drug, creatinga modular design that can have certain unique or complex componentsplaced on the exterior of the capsule 17 and maintain a communicationpathway. This also prevents the need for adhesive backing for theinternal portion of the tag 70 if the elasticity of the substrate 74provides sufficient rigidity to hold the tag 70 in the proper location.Additionally, the internal tag 70 can be created on a flat substrate asdescribed earlier, but the external portion of the tag may besufficiently simple to be printed, built-in, or otherwise attached tothe outside of the capsule 76. This embodiment also makes the process ofcreating multi-metal antennas or sensors simpler as only small strips ofmaterial need be placed on the outside of the capsule 70.

In another embodiment, the gastric sensor or other leads that areexposed to the outside of the capsule 76 are placed on the surface ofthe inner half 76A of the capsule, the portion to the capped by theother half 76B. The antenna 72 is then wrapped around the capsule 76,with the exposed antenna leads making contact with the metal extensionson the capsule's inner half 76A (see FIG. 13). In this way, the tag 70itself is concealed and only two very small metal strips are exposed,improving the appearance of the capsule 76.

Referring to FIG. 24, the internal component of the tag 43 is insertedinto the cap of the capsule and slides over the antennas 44, 79 printedor affixed to the smaller diameter portion of the capsule. When the tagis inserted into the smaller diameter portion of the capsule, via's orthrough holes 80 are punctured into the capsule to allow connection frominside to outside the capsule when necessary.

Tag Construction

Referring to FIGS. 25 and 26, in the preferred embodiment, the maincomponents of the tag 15 are a very small integrated circuit (IC) 71, ametal antenna 72, a gastrointestinal (GI) sensor/energy cell composed ofa specially coated GI sensor pad that doubles as an inlink antenna 73and a second metalic GI sensor pad 75, and a substrate 74.

The substrate 74 is composed of a specially coated paper. Non-whitened,low-weight papers are non-toxic and become softened in the GI tract M,E, S, D, I, R to allow for easy passage without risk of lodging as itpasses. These papers will then be coated with a pharmaceutical entericcoating known as “Eudragit”, which provides a smooth surface to allowprinting of antennas. Eudragit is also a pH-sensitive material that willdissolve in the colon R, allowing the tag 15 to remain active longenough to be detected before disintegrating.

The biocompatible antennas 72, 73 are printed on the substrate andpreferentially coated with Eudragit as described above to protect theantenna and prevent interaction with the antenna materials until the tagpasses into the colon R where it begins to disintegrate.

The GI sensor/energy cell includes the use of a zinc electrode 75 andsilver electrode 73 with special coatings as described previously. TheGI sensor is designed to restrict the bioavailability of the materialsto levels far below FDA, EPA, and/or recommended daily intakes. Thesimple GI sensor produces induced voltages from the voltaic battery whendifferent metals interact with the acidic GI fluids. Zinc foil ispreferably used for small scale production and is bonded to the tag 15using a conductive adhesive. An analog to digital converter within dataacquisition block 304 in the chip 20 is used to uniquely detect thesensor's response to GI fluid.

FIG. 26 shows the preferred embodiment of the tag, its size, and itsapproximate location of features. The tag 15 consists of four logicalcomponents: the tag body interface 73, the GI sensor 75, the tagintegrated circuit (IC) 71, and the out-link TX antenna 77. The tag bodyinterface 73 includes two in-link 50 pads (body contact pads) that are1-2 mm by 4 mm. The GI sensor includes a pad 75 that is approximately 1mm×5 mm. The out-link antenna 77 utilizes the rest of the availablespace. The tag IC 71 is shown in the inlay of the figure. FIG. 26Brepresents the tag after it is wrapped around a cylindrical object. Thein-link antenna pads are separated by the maximum available distance,which is 180 degrees across the capsule once the tag is wrapped aroundit. The out-link antenna is optimized for the required three dimensionalgeometry of the capsule (or pill) after attachment. The tag 15 materialsand construction conforms to all safety, regulatory, and manufacturingrequirements. The physical structure of the tag 15 and its relationshipto a medication capsule is shown in FIG. 27. Target Tag sizes are shownsuch as to conform to a size 0 capsule. Future generations are expectedto support smaller capsule geometries and tablets.

Reader

To minimize the size and power requirements of the external reader 11,in one embodiment it may not include the capabilities to transmitinformation via a cell system, wi-fi, or other wireless network.However, in another embodiment, the reader 11 can transmit data to astandard cell phone, pager, or other device as shown in FIG. 1 and asdescribed below with reference to FIG. 3, to allow for real-timeupdating of patient compliance and monitoring. Using a two part readersystem allows for a miniaturized on-body receiver 19 and a more powerfulmobile device 54 with a more sophisticated user interface for messagingand transmission to a global database. In such a two-part reader system,an on-body reader 11 has two communication systems, one 50, 52 tocommunicate with the tag 15 and one 56, 58 to communicate with themobile device (for example a bluetooth; see FIGS. 3 and 30 anddiscussion below). In such a system, the mobile device only requiresspecial software to operate as both a standard mobile device and afront-end user interface and wide area network (WAN) transmissioninterface.

The external reader 11 can be embodied in several forms. For example,the reader can be the wristband 111 of FIG. 28, or the patch 211 of FIG.29 that can be adhered to the skin like a bandage, an arm band, ahandheld device or the like. In some embodiments, it is advantageous forthe reader to have contact with the skin during a medication event. Itis also advantageous to design the reader to be readily available and/orworn to ensure it is present with the patient 16 for all medicationevents. Another form is the pill container 311 shown in FIG. 30 withcontacts 313 on the bottle holder 311 for skin contact during theingestion of the medication. A minimal user interface exists on thebottle holder 311 with a button to indicate ingestion has taken place312 and an indicator 313 to determine when the pill was detected. Thepatient 16 removes the medication from the container 311, ingests it,presses button 312 and holds the pill container 311 against the skinuntil the ingestion event is detected at the contacts 313 and theindicator 314 confirms that the tag 15 was detected in the body 16. Inother forms, the reader is also built into a mobile device such as acell phone, PDA, wrist watch, or into a memory card, dongle, or otheradd-on device that can be attached or inserted into a mobile unit.

Noting FIG. 30, each reader 11, 111, 211 and 311 has a small userinterface 227 that presents indicators of ingested medication beingdetected and/or the capabilities to indicate when medication should beingested. The readers are disposable or reusable, or contains portionsthat are disposable and reusable. The readers also preferably containmeans for storing the recorded data for downloading via USB or othermeans directly to a PC or other computing device. The readers are alsopreferentially rechargeable. In addition, for those applications wherethe readers do not need to be mobile, they may be built into a dongle orother means into a standard computer or laptop.

Continuing with FIG. 30, the reader comprises several RF/analogfront-end components interconnected with a digital processing core tohandle the communication protocols. The body interface or antennasubsystem 220 interfaces with the body 16 or media surrounding the body(e.g., air). It contains the antenna and or contact points to transmitthe inlink 50 data to the tag 15 and receive the outlink 52 data fromthe tag 15. In addition, the body interface subsystem 220 includes thesensors, contacts, or antennas necessary to acquire physiologic orbiometric data required to ensure the reader 11 is on the right patient16 and the tag 15 has been ingested by the right patient. The receivesubsystem 221 and transmission subsystem 222 contains the electronics todrive the antennas and/or receive data from the body interface andantenna subsystem 220. The uplink receive 225 and uplink transmit 226subsystems transmit data to and from an either a mobile device for widearea communication or directly to a wide area communication system suchas cell phone, wifi, or paging networks. The protocol and controlsubsystem 224 manages the communications of the outlink 52, inlink 50,uplink 56, and downlink 58 transmissions, controls the user interface227 and processes all data coming in and out of the reader 11. The userinterface system 227 provides information to the patient about when atag 15 has been detected, allows the patient 16 to initiate a manualdetection, provides indicators of when the pill 14 should be taken, andprovides other information to the patient.

The transmission subsystem 220 consists of a multiple modules. The firstmodule contains a high voltage modulator stage with a programmable lowfrequency carrier to galvanically couple RF signals into the body 16.The supply voltage of the modulator can be dynamically varied tosuperimpose in-link telemetry data to communicate with the tag on thepill. Digital input signals will be derived from the protocol andcontrol subsystem 224 tasked to handle communication protocols to andfrom the tag and also to and from an uplink/downlink transceiver 225,226 that wirelessly interconnects mobile devices to the reader 11. Thesecond module is a UHF receiver chipset used to demodulate out-link 52data from the tag 15. The receiver is used to downconvert the detectedout-link RF signals 52 for data extraction by the baseband processor.Preferably, all communication protocols between reader 11, tag 15 andmobile devices 54 are synchronized to a master clock generation moduleto ensure proper timing control.

Software System

True adherence improvement is likely to only be achieved when thepatient 16 is motivated to follow the prescribed regimen. By connectingthe patient with the medication, the pharmacodynamics (PD) andpharmacokinetics (PK), dose/response data, and their own reaction to themedications, patients become more interested in their regimen and becomemore adherent. The software system is preferentially implemented in asmart phone application that is linked to the reader 11 and theinformation provided by the uplink/downlink data. In a preferredembodiment, the software shows estimated blood levels of the drug ofinterest based on the known patient information and medical informationstored in the system, as well as the exact timing and doses of themedication taken by the patient. The software shows the patients howmissing doses or improperly taking their medication affects theirsimulated blood levels, drug effectiveness, and how it changes theirphysical responses to the medication.

Other embodiments include personalized calendars that a list eachmedication and dosage listed under the following 4 times periods:Morning, Noon, Evening, and Bedtime. If a patient does not take theirmedicine, they are asked to write the reason. It also lists any specialinstructions to help prevent adverse effects resulting in decreasedmedication adherence. The software also contains a list of abbreviatedinstructions on how to use and monitor each drug so that the patientunderstands the benefit and risk of each drug. The software also allowsthe pharmacist to enter how many days late the patient comes to thepharmacy for a refill of chronically taken medication. If the adherencerate is unsatisfactory, the pharmacist is presented with various optionson how to enhance adherence through patient education programs designedfrom well documented motivational interview techniques.

The Personalized Medication Adherence Registry (PMAR) is a mobilesoftware system that receives medication adherence data from the patientand device links, then presents it to the patient and healthcareproviders in an extremely quick and easy to understand format. Thelargest group that will benefit from PMAR are those patients takingmultiple chronically administered medications that are essential towellness. Another important population are patients who are receivingmedications that create frequent or severe adverse drug reactions(ADRs). Typical examples of healthcare providers are all physicians,pharmacists, nurse practitioners, physician assistants, clinical trialpersonnel, and any other health related professions who advise, monitoror treat patients with medications.

When patients visit their physician or other health care providers, theyare usually asked to produce a comprehensive, up-to-date, and accuratelist of all their medications including the name of the drug, the dosagestrength, and the directions for use. This list can become extremelycomplex very quickly and difficult to recall. This list is immenselyvaluable when a patient is traveling and in an accident. It may be lifesaving if this medication list can be produced as quickly as possiblewith all the required details. Having an electronic copy immediatelyavailable can save the patient time and money while improving theirhealth and possibly preventing an inappropriate drug relatedcatastrophe. A common example is when one of over 20 million Americanswith diabetes becomes extremely weak in a public place. If he/she hasrecently taken his blood sugar lowering agent, a liquid withconcentrated sugar e.g. a soft drink or orange drink may save theirlife. The patient must provide their username and password to allowothers access to this encrypted information. Since this protectedinformation resides on their cell phone, access to cellular service isnot required. A back-up of all this protected information can also beaccessed by the patient and any healthcare provider, family member orclose friend who has access.

If the patient has access to the Internet via their cell phone orpersonal computer, they will be able to click a drug from their druglist and be linked to drug-specific information in Wikipedia. They willbe reminded to print the information and have it validated for itsaccuracy and personalized application to their situation based uponvarious factors that are relevant, e.g., all their existing diseasestated, medication list, age, sex, weight, diet, and exercise program.

Medication and Refill Reminders

The Reminder feature of PMAR provides a timely visual and auditorynotice to the patient via their mobile phone allowing the customer to bealerted for each of their scheduled medications. PMAR is easilycustomizable as to each patient's preference as to how they are to bereminded and the sound/vibrate/visual notification rules governing thereminder system. They can reminded to take all their prescriptionmedications (Rx's), OTCs, herbal medications, and nutritionalsupplements. This information is stored in their cell phone calendar andalso does not require access to a cellular network.

PMAR will also remind the patient several days prior to completing theirmedication that it is time to obtain a new refill or if they areprobably almost out of their OTC, herbal, and nutrition supplement. Thisprevents one of the leading causes of proper medication adherence. Thesereminders are based upon the date of the last refill and whether theyreceived a weekly, monthly, or quarterly refill.

Although reminder systems are not uncommon, when coupled to compliancemonitoring systems, additional features become possible. For example, ifmedications are not ingested when requested, a series of reminders oralerts can be sent starting with the patient and following up withfamily, care givers, doctors, pharamcists, drug trial monitors andadministrators. If necessary, the system or support personnel can callor visit the patient to ensure that there are no problems and that thepatient is taking the medication regularly.

Adverse Drug Reaction Report (ADR)

When the patient is reminded to take their medication, one of theiroptions will be to choose from a list of common side effects and ADRs todocument if they have experienced a recent ADR and if they stoppedtaking their medication secondary to the ADR. This often happens withoutthe pharmacist or physician being aware. This will assist healthcareproviders in determining the cause of patient non-adherence and promptthem to possibly decrease the dose or select an alternative medication.This feature alone can help decrease many avoidable hospitalizations.

Other Features

Referring again to FIG. 1, as an alternate to detection of the pill inthe gastrointestinal system, it is also possible to detect a pill 30 asit passes through the esophagus E using a sensor 32 designed to fitaround the neck 33. Preferably, this sensor 32 takes the form of acomplete circle around the neck 33, a partial, horseshoe-like enclosure,or a simple device held against the neck 33. The sensor 32 detects allembodiments of the pill 30 described elsewhere as it passes through theesophagus E into the stomach S. The embodiments in which the sensor 32forms a semi- or full circle around the neck 33 also improve thesignal-to-noise ratio over a sensor that is simply held in front of thepatient. There is also less dependence on digestive mechanisms,providing less design restrictions on the pill itself.

The neck sensor operates in all the same ways as the gastrointestinalreader 11, but also allows for other, possibly advantageous, protocols.For the case in which multiple pills must be detected, a protocol inwhich the patient takes one pill at a time can be employed. In thisapproach, only one pill will occupy the esophagus E at any time, whichimproves the sensor's capability to identify and tally dosage.

The above specification and the drawings have been used to disclose anumber of embodiments of this invention. Specific terms have been usedin a descriptive sense only and not for purposes of limitations. It willbe appreciated by those skilled in the art that various changes andmodifications can be made in the above described embodiments withoutdeparting from the spirit and scope of this invention.

What is claimed:
 1. An electronic system for monitoring a patient'singestion of an ingestible delivery device, the electronic systemcomprising: an ingestible delivery device; an electronic circuitassociated with the ingestible delivery device and configured togenerate and transmit one or more radio frequency signals to indicatethe ingestion of the delivery device; and an electronic readerpositioned externally to the patient and configured to receive one ormore radio frequency signals from the electronic circuit.
 2. Theelectronic system of claim 1, further comprising at least one remotedevice configured to receive information from the electronic reader andgenerate data indicative of the patient's ingestion of the deliverydevice based at least on the information received from the electronicreader.
 3. The electronic system of claim 2, wherein the at least oneremote device is further configured to upload the data indicative of thepatient's ingestion of the delivery device in at least one remotedatabase.
 4. The electronic system of claim 1, wherein the electroniccircuit is configured to generate the one or more radio frequencysignals in accordance with a plurality of programmable data fields,wherein at least a portion of the plurality of programmable data fieldsare configured to facilitate at least the electronic reader to detectthe presence of the delivery device within the patient's body.
 5. Theelectronic system of claim 1, wherein the delivery device is associatedwith a unique identifier, and the electronic circuit is configured totransmit data representing the unique identifier to the electronicreader.
 6. The electronic system of claim 5, wherein the electronicreader is configured to receive and differentiate radio frequencysignals from multiple electronic circuits that are within the patient'sbody and are simultaneously communicating with the electronic reader. 7.The electronic system of claim 1, wherein the delivery device containsone or more medicines.
 8. An ingestible electronic system for trackingingested medication in a patient's body, the ingestible electronicsystem comprising: an electrically insulated substrate; an electroniccircuit fitted to the substrate and configured to generate and transmitone or more signals in accordance with a plurality of programmable datafields, wherein at least a portion of the plurality of programmable datafields are configured to facilitate at least a detection of a status ofthe delivery device within the patient's body; and an antenna disposedacross the substrate and electrically coupled to the electronic circuitfor transmitting the one or more signals.
 9. The ingestible electronicsystem of claim 8, wherein the substrate comprises multiple layers ofcoatings for tracking the substrate when the substrate is exposed todifferent solutions in the patient's body.
 10. The ingestible electronicsystem of claim 8, further comprising a plurality of sensors coupledwith the electronic circuit, wherein at least one sensor of theplurality of sensors is configured to provide varying inputs to theelectronic circuit dependent upon a location of the at least one sensorin the patient's body.
 11. The ingestible electronic system of claim 8,wherein the electronic circuit is configured to transmit the one or moresignals to an electronic reader positioned externally to the patient'sbody.
 12. The ingestible electronic system of claim 11, wherein theelectronic reader comprises a first subsystem for communicating datawith the electronic circuit, and a second subsystem for communicatingdata with at least one remote device.
 13. A method for monitoring apatient's compliance with a medication program, the method comprising:positioning an electronic reader externally to a patient; providing to apatient a medicine delivery device comprising an electronic circuit;having the patient ingest the medicine delivery device; transmitting, bythe electronic circuit to the electronic reader, one or more radiofrequency signals that are generated after the patient ingests themedicine delivery device; and connecting at least one remote device tothe electronic reader, wherein the at least one remote device isconfigured to receive the one or more radio frequency signals from theelectronic reader and generate data indicative of the patient'scompliance with the medication program based at least on the one or moreradio frequency signals.
 14. The method of claim 13, wherein the one ormore radio frequency signals are generated in accordance with aplurality of programmable data fields, wherein at least a portion of theplurality of programmable data fields are configured to facilitate atleast the electronic reader to detect the presence of the medicinedelivery device within the patient's body.
 15. The method of claim 13,further comprising: associating a unique identifier with the medicinedelivery device; and transmitting, by the electronic circuit, datarepresenting the unique identifier of the tag to the electronic reader.16. The method of claim15, further comprising: receiving anddifferentiating, by the electronic reader, multiple radio frequencysignals from multiple electronic circuits that are within the patient'sbody and are simultaneously communicating with the electronic reader.17. The method of claim 13, wherein the electronic reader comprises ahandheld mobile device that is positioned externally to the patient. 18.A non-transitory computer-readable medium having one or moreinstructions which, when executed by one or more processors of acomputing device, causes the one or more processors to performoperations comprising: receiving, by the computing device, informationrelating to a medicine delivery device from an electronic readerpositioned externally to a patient within a distance after the patientingests the medicine delivery device, the medicine delivery devicecomprising an electronic circuit, the electronic circuit beingconfigured to transmit the information relating to the medicine deliverydevice to the electronic reader while the electronic circuit beingexposed to different solutions inside the patient's body; uploading theinformation relating to the medicine delivery device in real-time to atleast one remote database; receiving drug specific and patient specificinformation from various sources; generating data indicative of thepatient's compliance with a medication program based at least on theinformation relating to the medicine delivery device and the drugspecific and patient specific information; and presenting the data tothe patient.
 19. The non-transitory computer-readable medium of claim18, wherein the at least one remote database is accessible by at leastone of a healthcare provider, physician, clinical trial personnel,family member of the patient, pharmacist, or insurance company.
 20. Thenon-transitory computer-readable medium of claim 18, wherein the datapresented to the patient comprise a list of common side effects andadverse drug reactions for the patient.